High Dynamic Range Mammography Using a Restricted Dynamic Range Full Field Digital Mammogram

ABSTRACT

Methods of imaging a breast comprising acquiring a sequence of image data sets having differing exposure parameters; and combining the image data sets into a mammography image having greater dynamic range than the dynamic range of any single component image data set. Disclosed methods may further comprise determining an exposure parameter of one or more component image data sets prior to acquiring the sequence of image data sets. The step of determining an exposure parameter of one or more component image data sets may comprise determining exposure duration or an exposure irradiation level. Also disclosed are mammography apparatus and systems to obtain images according to the disclosed methods.

TECHNICAL FIELD

The embodiments disclosed herein relate to apparatus and methods ofexposing and processing high dynamic range images from digitalflat-panel x-ray detectors.

BACKGROUND

Flat panel detectors are used in mammography for screening anddiagnostic imaging. In both cases it is desirable to see features overthe full extent of the breast, from the thickest and most dense tissuenear the chest wall and in the centre of the breast, such asfibroglandular breast tissue, to the thinnest and least dense tissuenear the skin boundary, such as fat and skin. A full-breast mammographyimage is thus obtained from x-ray signals of wide dynamic range, rangingfrom the maximum intensity of a nearly unobstructed x-ray beamtransmitted through the skin boundary, to the substantially weakenedsignal transmitted through dense tissue. The presentation of a useablewide dynamic range image is achieved in film-based methods by the use ofhigh-latitude film, which has a non-linear response and can tolerateover-exposure.

Digital mammography however, typically uses flat panel detectors thatbehave differently than film when exposed to varying intensities ofexposure. One type of flat panel detector employs CMOS image sensors,which have an inherently linear response with poor latitude. Inparticular, sensors with small well size respond to overexposure bysaturating. Saturation occurs when the sensor pixel values reach aconstant maximum as a certain signal level is exceeded, and all dataabove this level is lost. CMOS image sensors however, are advantageousfor mammography in that a well designed sensor will generate a low levelof electronic noise, which provides enhanced contrast in dense breasttissue when compared to other types of flat panel detector.

The visibility of structures within the breast tissue is limited by thecontrast-to-noise ratio (CNR) of the imaging system. The contrast of anobject in a mammography image depends on the density of the object, thetotal x-ray attenuation provided by the object and the soft tissue inthe breast, the x-ray spectrum used (photon energy and tube voltagekVp), scattered radiation and the display conditions. In addition, anon-saturating mammography exposure must be scaled to the unobstructed(air) transmission value. This can leave clinically significant areas ofinterest (denser tissue) underexposed, with consequently poor CNR.

The embodiments disclosed herein are directed toward overcoming one ormore of the problems discussed above.

SUMMARY OF THE EMBODIMENTS

The disclosed embodiments include a method and associated apparatuswhich combines separate images of the breast into a single Full FieldDigital Mammogram (FFDM), where the FFDM is composed of pixels oflimited electron-well size that do not innately provide sufficientdynamic range to acquire a single-exposure mammogram showing detail inall relevant portions of a breast.

The described images are taken as a set of predetermined exposures anddo not use image data recursively. The component images are thencombined into a single presentation image using selected imagerecombination techniques. The disclosed methods differ from otherpreviously taught methods in several aspects. For example, the disclosedmethods apply to the field of mammography where every part of thebreast, from dense tissue to near-transparent skin edges, must be imagedwith a high level of image quality. In addition, the disclosed methodsapply specifically to digital flat panel detectors where the electronwell depth is designed to be below around 500 electrons per squaremicron, for minimisation of readout noise, which increases as a functionof full well capacity.

Embodiments include a method of imaging a breast comprising acquiring asequence of image data sets having differing exposure parameters; andcombining the image data sets into a mammography image having greaterdynamic range than the dynamic range of any single component image dataset. Disclosed methods may further comprise determining an exposureparameter of one or more component image data sets prior to acquiringthe sequence of image data sets. The step of determining an exposureparameter of one or more component image data sets may comprisedetermining exposure duration or an exposure irradiation level. Thedetermination of an exposure parameter may be based upon one or more ofx-ray beam quality, x-ray beam intensity, information about the imagedobject, breast thickness, patient age and the response of the detector.

The disclosed methods of imaging a breast of may be implemented using adigital flat panel detector designed for the minimisation of readoutnoise. For example, the digital flat panel detector electron welldensity can be designed to be below around 500 electrons per squaremicron.

An alternative embodiment is an apparatus for imaging a breastcomprising: an x-ray source; an x-ray detector; and image processingapparatus configured to acquiring a sequence of image data sets havingdiffering exposure parameters and combine the image data sets into amammography image having greater dynamic range than the dynamic range ofany single component image data set. The apparatus may comprise adigital flat panel detector designed for the minimisation of readoutnoise. for example, the digital flat panel detector electron welldensity can be designed to be below around 500 electrons per squaremicron.

An alternative embodiment is a system for obtaining a high dynamic rangeimage of a breast, the system comprising: a mammography imaging device;and a data processing device providing for the combination of image datahaving lesser dynamic range obtained with the mammography imaging deviceinto a mammography image having greater dynamic range.

An alternative embodiment is a computer readable storage medium havinginstructions stored thereon, wherein the instructions are implemented toprovide a method of imaging a breast comprising: acquiring a sequence ofimage data sets having differing exposure parameters; and combining theimage data sets into a mammography image having greater dynamic rangethan the dynamic range of any single component image data set.

In addition to the exemplary aspects and embodiments described above,further aspects and embodiments will become apparent by reference to thedrawings and by study of the following descriptions.

BRIEF DESCRIPTION OF THE DRAWINGS

Exemplary embodiments are illustrated in referenced figures of thedrawings. It is intended that the embodiments and figures disclosedherein are to be considered illustrative rather than limiting

FIG. 1 is a schematic cross-section of a breast B positioned for amammogram.

FIG. 2 is a graphic representation of a linear, low-gain response from adigital detector, where 100% of the digital pixel value corresponds tonominal zero x-ray attenuation.

FIG. 3 is a graphic representation of a linear, high-gain response froma digital detector, where 100% of the digital pixel value corresponds toa transmission TMAX which is within the transmission range of thebreast.

FIG. 4 is a graphic representation of a combination of three exposuresof varying gain.

FIG. 5 is a graphic representation of threasholded image data from FIG.4.

FIG. 6 is a graphic representation of combined image data from FIG. 4and FIG. 5.

FIG. 7 is a graphic representation of two component exposure that may becombined to form a single HDR mammogram.

FIG. 8 is a graphic representation of two component exposure that arenot suitable for combination to form a single HDR mammogram since theSNR of one sub-image is too low.

FIG. 9 is a graphic representation of three component exposure that maybe combined to form a single HDR mammogram.

FIG. 10

FIG. 11 is two x-ray images of a breast taken at lower and higherexposures.

FIG. 12 is a magnified view of the two x-ray images of FIG. 11.

FIG. 13 is two x-ray images showing an average of the lower exposure andhigher exposure of FIG. 11 and a weight blending of the lower exposureand higher exposure of FIG. 11.

FIG. 14 is a magnified view of the two x-ray images of FIG. 13.

FIG. 15 is an x-ray image created from the weight blended breast imageof FIG. 14 after image enhancement.

FIG. 16 is a functional block diagram representation of a data/imageprocessing system associated with a mammography system.

DETAILED DESCRIPTION

Unless otherwise indicated, all numbers expressing quantities ofingredients, dimensions reaction conditions and so forth used in thespecification and claims are to be understood as being modified in allinstances by the term “about”.

In this application and the claims, the use of the singular includes theplural unless specifically stated otherwise. In addition, use of “or”means “and/or” unless stated otherwise. Moreover, the use of the term“including”, as well as other forms, such as “includes” and “included”,is not limiting. Also, terms such as “element” or “component” encompassboth elements and components comprising one unit and elements andcomponents that comprise more than one unit unless specifically statedotherwise.

The contrast of a region in an object in a mammography image depends onthe density of the region, the x-ray attenuation of the region in thebreast, the x-ray spectrum (photon energy, filtration, tube current,exposure length and tube voltage kVp), scattered radiation and thedisplay conditions. The noise present in the image is the vector totalof all noise processes contributing in the image chain. These noisecontributors include:

-   i. Statistical variation (shot noise) of incident transmitted x-ray    photons-   ii. fixed pattern noise due to pixel offset variations,-   iii. fixed pattern noise due to pixel gain variations,-   iv. fixed pattern noise due to x-ray conversion and attenuation    variations across the image applied by the scintillator and the    covering materials,-   v. temporal noise generated in the pixel during readout,-   vi. temporal noise generated in amplifier stages prior to    analogue-to-digital conversion,-   vii. quantization noise introduced by the analogue-to-digital    conversion,-   viii. temporal noise introduced by rounding in subsequent data    processing, and-   ix. structural and temporal noise introduced by the display medium.

Noise sources ii, iii, iv, vi, vii, viii and ix can be addressed usingknown image acquisition, image processing or data manipulationtechniques.

Noise source i; shot noise, is a function of the dose delivered to thebreast, and the efficiency of the x-ray to photoelectron conversion. Thedelivered dose per image is limited by clinical restrictions relating topatient safety.

Noise source v; readout noise, is significant where a pixel's electricaloutput is low relative to its maximum value. Readout noise is limited bythe design of the sensor and its physical limits. Readout noise isadditive noise arising from the noise characteristics of semiconductordevices, which has the following general form:

${S(\omega)} \propto \left\{ \begin{matrix}\omega^{- b} & {\omega < \omega_{m\; i\; n}} & {\beta > 0} \\A & {\omega_{m\; i\; n} < \omega < \omega_{m\; {ax}}} & \; \\\omega^{\alpha} & {\omega > \omega_{m\; {ax}}} & {\alpha > 0}\end{matrix} \right.$

where A, α and β are constants, and ω is the readout frequency. ω_(min)is the 1/f noise ‘knee’ below which the noise has a mainly 1/fcharacteristic.

In addition, there is a thermal noise contribution with theoreticallower limit

σ_(KTC)=√(kT/C)

where k is the Boltzmann constant, T is the absolute temperature and Cis the capacitance of the pixel.

It can be seen from the above that thermal noise increases withcapacitance. Therefore, in general, the pixel capacitance or ‘well size’should be minimised to reduce total readout noise. However, well sizeminimization also reduces the number of photoelectrons that can berecorded by a single pixel readout, since the voltage across thecapacitor is limited to an upper value determined by the sensor design,and the voltage is proportional to the number of photoelectrons:

V _(MAX) =Ne ⁻ /C

where N is the number of photoelectrons, and C is the capacitance. Thepractical effect of a small well size is that the sensor saturates(V=V_(MAX)) at a lower x-ray exposure.

Mammography, unlike most other types of radiography, must presentclinically significant detail over the entire target including skinboundary. Mammography requires a high dynamic range from the imagingdevice in order to produce acceptable image quality contrast to noiseratio (CNR) from all parts of the breast within an exposure. However,high X-ray dynamic range requires a large well size, while the lowreadout noise that provides good contract in dense breast tissuerequires a low well size. There is therefore a compromise required: alow noise detector does not provide a wide x-ray dynamic range, and ahigh dynamic range detector presents greater noise issues.

In particular, the read-out noise per pixel of a CMOS detector increaseswith the well capacity of the pixel. The maximum signal obtainablebefore saturation increases linearly with the well capacity. In order tomaximize the signal-to-noise ratio for a given exposure dose, it can beshown that it is better to acquire multiple frames using alow-well-capacity pixel design, rather than a single frame using ahigh-well-capacity design, since the increase in total readout noisewhich results from multiple frame reads is more than offset by thereduction in readout noise due to the smaller well capacity. Thereforeit is beneficial to use multiple-frame image acquisition in mammographyas disclosed herein. In summary, multiple frame acquisition can beexploited to solve a problem which is particular to mammography, whichis the problem of acquiring and presenting a clinically useful imagefrom a subject which has a very wide x-ray transmission contrast ratio.

The problems unique to high dynamic range mammography using digitalsensors may be more fully appreciated with respect to FIGS. 1-4. FIG. 1shows a cross-section of a breast 10 positioned for a mammogram. Anx-ray transparent compression plate 12 and a detector assembly 14 holdthe breast immobile during x-ray exposure from a source 16. Theresulting projection onto the detector 14 has a wide range of imageintensities, as the x-rays are attenuated by different amounts rangingfrom no tissue attenuation (H), through partial attenuation (G), tomaximum attenuation (F) where the rays pass through the thickest,densest tissue.

FIG. 2 shows a linear, low-gain response from a digital detector, where100% of the digital pixel value corresponds to nominal zero x-rayattenuation (air only). At an x-ray transmission T₁, the signal S₁ islarge enough to represent usable clinical data. This is the linearresponse of a typically implemented Full Field Digital Mammography(FFDM) detector idealised for mammography where the maximum transmission(air with no tissue) generates the maximum response. Below transmissionlevel T₁, in even denser regions of the breast for example, the CNR isunacceptable due to insufficient signal relative to readout noise.

FIG. 3 shows a linear, high-gain response from a digital detector, where100% of the digital pixel value corresponds to a transmission T_(MAX)which is within the transmission range of the breast. The same effectwould occur if the exposure dose, the x-ray beam energy, the x-ray tubecurrent, or a combination of one or more of these parameters wereincreased. Any transmission higher than T_(MAX) is represented by auniform, saturated pixel output at 100%. The usable signal level S₁ nowcorresponds to a lower transmission level, T₂. An exposure such as isrepresented in FIG. 3 can be taken to acquire data which is missing fromthe exposure represented in FIG. 2 where the transmission level is lessthan T₁ and was too low to produce useable data. Such a mammogram wouldshow image detail in denser regions but would show a monochrome greyvalue in less dense regions.

FIG. 4 shows a combination of three exposures of varying gain; exposures(ad) and (ab) are the exposures from FIG. 2 and FIG. 3 respectively.Above the transmission level T₁, the usable response is indicated bygrey sections of each response curve. A third exposure (ac) is added, tofill in the midrange response between ad and ab. A third or successiveintermediate exposure is not essential to the disclosed embodiments butmay be used where there is a wide gain difference between the low andhigh-gain exposures.

As noted above, a set of two or more exposures with different exposuredoses may be taken to extend the dynamic range of a selected sensor. Atleast one of the exposures should be capable of registering the airvalue (100% transmission) before saturation, as illustrated in FIG. 2.As described in detail below, the set of exposures may be prescribedaccording to a priori knowledge of the detector noise characteristicsand the transmission of the densest region of interest in the breast.

In FIG. 4, the grey portion of each response curve (curve segments 40,42 and 44 respectively) represent usable data. The portions of eachresponse curve at 100% signal have no data because of sensor saturation.Finally, the portions of the response curves 46 and 48 have no usefuldata because the SNR due to readout noise is lower than 1, meaning thatthe data would contribute more noise than signal if it were used tocompute a final result.

The usable data, for example data represented by response curves 40, 42and 44 on FIG. 4, can be combined or fused into a high quality imageusing various techniques. The techniques include methods such as tonemapping and cross correlation. An example of a simple method of fusingis thresholding and addition. FIG. 5 graphically illustrates such amethod using the data of FIG. 4. In the FIG. 5 representation, there isa lower noise thresholding process. In particular, the noisiest portionsof data as illustrated on FIG. 4 (represented by response curve portions46 and 48) are replaced by constants, shown as line 50 of FIG. 5.Therefore:

$S^{\prime} = \left\{ \begin{matrix}S_{1} & {S < S_{1}} \\S & {S > S_{1}}\end{matrix} \right.$

The FIG. 5 representation also illustrates a numerical upper saturationthresholding process, represented by the upper line 52, since the actualsaturation limits on the sensor may be subject to noise. Accordingly:

$S^{\prime} = \left\{ \begin{matrix}S & {S < S_{2}} \\S_{2} & {S > S_{2}}\end{matrix} \right.$

As shown in FIG. 6, adding the useful signals 40, 42 and 44 from allthree images represented in FIGS. 4 and 5 yields a nonlinear butmonotonic response to density, which demonstrates latitude, i.e. areduction in sensitivity as the signal increases. X-ray filmdemonstrates a similar property of latitude.

Further refinements to this method can provide for different nonlinearresponses. One side-effect of combining images in this way is thediscontinuity in SNR, and therefore image quality, near the thresholdsT_(MAX1) and T_(MAX2). This may be presented as contouring artifacts orbands visible as the density changes smoothly over the image. Knownmethods of image processing may be used to even out this discontinuity.

According to one embodiment, multiple exposures may be acquired withinthe duration of a single x-ray exposure. An FFDM device maybe programmedto acquire a sequence of images, the only difference between imagesbeing the frame integration time, which corresponds to the gain of

$\frac{\delta \; S}{\delta \; T}$

mager, or a sequence of exposures may be determined such that themaximum image information is acquired using the minimum duration ofx-ray exposure. This can be achieved by definition of a threshold whereimage information contributes more noise than signal. Alternatively, asequence of images may be obtained by varying the exposure level isbetween images, by varying the x-ray beam energy, the x-ray tube currentor a combination of one or more of these parameters. To allow a sequenceof images to be acquired without extending the duration of the imaging,the detector used must have a high read-out speed, for example 5 or moreframes per second. Lengthening the imaging time would increase the riskof patient motion.

As noted above, two essential image features or regions in a FFDM aredense tissue information and substantially less dense skin edgeinformation. As illustrated in FIG. 7, skin edge information may beacquired from a first exposure [1] which is short enough so that theunobstructed (air) values do not cause sensor saturation. The exposuretime for exposure [1] can be determined from given data about the x-raybeam quality and intensity, and is not dependent on the image object.

Dense tissue information can be acquired through a second, longer ormore intense exposure [2]. The exposure time for exposure [2] can bedetermined from given data about the x-ray beam quality and intensity,information about the imaged object (for example breast thickness,patient age, etc), and the response of the detector. Alternatively theexposure time for exposure [2] can be determined from analysis ofexposure [1], where the correct exposure time is extrapolated fromanalysis of the trial exposure as follows:

$t_{2} = \left\{ \begin{matrix}{t_{1} \times {S_{DT}/S_{D\; 1}}} & {t < t_{M\; {AX}}} \\t_{M\; {AX}} & {t > t_{M\; {AX}}}\end{matrix} \right.$

where t₁ is the first exposure time [1], S_(DT) is the required signallevel in the densest part of the image, S_(D1) is the signal level inthe densest part of the image from the first exposure [1], and t_(MAX)is an upper limit on exposure time imposed by restrictions on radiationdose.

In some cases, two exposures will be sufficient if, in regions where thetransmission is high enough to saturate the second exposure (T>T₁), thefirst exposure has enough signal to yield sufficient SNR (signal>S_(T),where S_(T) is the minimum signal to yield acceptable SNR). This is thecase illustrated in FIG. 7. In other cases, one or more additionalimages [3] may be needed if, as shown in FIG. 8, the SNR from image [1]at transmission=T₁ is too low. This case is illustrated in FIG. 9. Theset of images and exposure times can be thus be determined according toa logical process.

The input parameter T₁ can be determined by a priori knowledge of dataconcerning the imaged breast, using clinical data and look-up tablesbased upon the patients' age, breast thickness, the x-ray beam quality,etc.

The methods generally described above are more specifically describedwith respect to FIG. 10. Two or more sub-images, at different levels,are acquired in rapid succession on a single X-ray exposure at eachselected view angle. These sub-images are then combined into a finalimage where both dense-tissue information and skin-edge information arepresented. The exposure level is varied between images by varying theexposure duration, the x-ray beam energy, the x-ray tube current or acombination of one or more of these parameters.

Within the imager device, the pixel data from each image is bounded to aconstant value N_(SAT) which is lower than the saturation value of theimage. A lower value is used because each pixel has a slightly differentsaturation level, and a global value ensures consistency across allpixels. Pixels with values above N_(SAT) will therefore not contributedata to the composite image. The bounded image data is then combined.This can be done in a number of ways, for example:

(a) As shown in FIG. 10, a summation of a set of images with differentexposure levels may be performed where the images have equal weights;this avoids contouring effects in the combined image as noted above. Forsub-images 102, 104 and 106 (FIG. 10) the combined image I_(c) is asummation:

I _(C)=Σ_(n=1) ^(M) Ī _((n))

(b) Alternatively, summation of each image may be performed according toa weighting map, where the contribution from each image is varied over Xand Y, according to some means of a priori image content analysis.

Example

A practical implementation of an image fusion process, which applies tomammography, is as described below with respect to FIGS. 11-15. Thedisclosed method identifies the best quality of each image, beforecombining the set using a scalar weighting values.

Appropriate scalar weight values are obtained from the relative exposureand contrast information which are taken directly from each image. Oncethe weight values are determined, the set of ‘N’ images is combinedusing weight blending:

B _(ij)=Σ_(k=1) ^(N) Ŵ _(ij,k) J _(ij,k)  (1)

where J and W are pre-processed image and weight respectively. Thepre-processed image is obtained by:

J=(L−L _(min))/(L _(max) −L _(min))  (2)

where:

$L = \left( \frac{I}{I_{m\; {ax}}} \right)^{1/2}$

with ‘I’ being the input image.

The weight in equation (1) is normalized so that the sum of all weightsof each pixel across the ‘N’ number of images is one:

$\begin{matrix}{{\hat{W}}_{{ij},k} = \frac{W_{{ij},k}}{\sum\limits_{n = 1}^{N}W_{{ij},n}}} & (3)\end{matrix}$

Here, the weight ‘W’ is determined by the exposure level and contrastmeasurement of each pixel.

W _(ij,k)=(E _(ij,k))^(we)(C _(ij,k))^(wc)  (4)

For the contrast ‘C’, absolute value of Laplacian filtering is used tohighlight the edges. For the exposure level measurement ‘E’, the pixelswith values closer to the central region of 0.5 is given more weight.This is done through a Gaussian curve. In this case, the effect of thepixels with intensities near the 0 (under-exposed) and 1 (over-exposed)are reduced. The weights therefore are obtained using:

$\begin{matrix}{W_{i,j} = {\exp\left( {- \frac{\left( {J_{ij} - 0.5} \right)^{2}}{2\sigma^{2}}} \right)}} & (5)\end{matrix}$

Experimental results illustrated in FIGS. 11-15 show that the weightexponent values, in Equation (4), of we=0.2 and wc=0 produces goodresults. In particular, FIG. 11 shows a lower-exposure breast image 112and the same breast in a higher exposure image 114. FIG. 12 shows theimages of FIG. 11 in a magnified view. FIG. 13 is an average of thelower exposure 112 and higher exposure 114 (producing image 116) and aweight blending of the lower exposure 112 and higher exposure 114prepare according to the methods described above (producing image 118).FIG. 14 shows the images of FIG. 13 in a magnified view. FIG. 15 is animage 120 created from the weight blended breast image 118 after imageenhancement.

Some embodiments disclosed herein include a system or apparatus having adata processing or image processing device or element. Onerepresentative data processing or image processing device is illustratedin FIG. 16. The data/image processing system 122 is shown comprisinghardware elements that can be electrically coupled via a bus 124 (or mayotherwise be in communication, as appropriate). The hardware elementsmay include one or more processors 126, including without limitation oneor more general-purpose processors and/or one or more special-purposeprocessors (such as digital signal processing chips, graphicsacceleration processors, and/or the like); one or more supplementalinput devices 128, which can include without limitation a mouse, akeyboard and/or the like; and one or more output devices 130, which caninclude without limitation a display device, a printer and/or the like.

The data/image processing system 122 may further include (and/or be incommunication with) one or more storage devices 132, which can comprise,without limitation, local and/or network accessible storage, and/or caninclude, without limitation, a disk drive, a drive array, an opticalstorage device, solid-state storage device such as a random accessmemory (“RAM”) and/or a read-only memory (“ROM”), which can beprogrammable, flash-updateable and/or the like. Such storage devices maybe configured to implement any appropriate data stores, includingwithout limitation, various file systems, database structures, and/orthe like.

The data/image processing system 122 might also include a communicationssubsystem 134, which can include without limitation a modem, a networkcard (wireless or wired), an infra-red communication device, a wirelesscommunication device and/or chipset (such as a Bluetooth™ device, an802.11 device, a WiFi device, a WiMax device, a WWAN device, cellularcommunication facilities, etc.), and/or the like. The communicationssubsystem 134 may permit data to be exchanged with a network (such asthe network described below, to name one example), with other computersystems, and/or with any other devices described herein. In manyembodiments, the data/image processing system 122 will further comprisea working memory 136, which can include a RAM or ROM device, asdescribed above.

The data/image processing system 122 also may comprise softwareelements, shown as being currently located within the working memory136, including an operating system 138, device drivers, executablelibraries, and/or other code, such as one or more application programs140, which may comprise computer programs provided by variousembodiments, and/or may be designed to implement methods, and/orconfigure systems, provided by other embodiments, as described herein.Merely by way of example, one or more procedures described with respectto the method(s) discussed below might be implemented as code and/orinstructions executable by a computer (and/or a processor within acomputer); in an aspect, then, such code and/or instructions can be usedto configure and/or adapt a general purpose computer (or other device)to perform one or more operations in accordance with the describedmethods.

A set of these instructions and/or code might be encoded and/or storedon a non-transitory computer readable storage medium, such as thestorage device(s) 132 described above. In some cases, the storage mediummight be incorporated within a computer system, such as the data/imageprocessing system 122. In other embodiments, the storage medium might beseparate from a computer system (i.e., a removable medium, such as acompact disc, etc.), and/or provided in an installation package, suchthat the storage medium can be used to program, configure and/or adapt ageneral purpose computer with the instructions/code stored thereon.These instructions might take the form of executable code, which isexecutable by the data/image processing system 122 and/or might take theform of source and/or installable code, which, upon compilation and/orinstallation on the data/image processing system 122 (e.g., using any ofa variety of generally available compilers, installation programs,compression/decompression utilities, etc.) then takes the form ofexecutable code.

The terms “machine readable medium” and “computer readable medium,” asused herein, refer to any medium that participates in providing datathat causes a machine to operation in a specific fashion. In anembodiment implemented using the data/image processing system 122,various computer readable media might be involved in providinginstructions/code to processor(s) 126 for execution and/or might be usedto store and/or carry such instructions/code (e.g., as signals). In manyimplementations, a computer readable medium is a non-transitory,physical and/or tangible storage medium. Such a medium may take manyforms, including but not limited to, non-volatile media, volatile media,and transmission media. Non-volatile media includes, for example,optical and/or magnetic disks, such as the storage device(s) 132.Volatile media includes, without limitation, dynamic memory, such as theworking memory 136. Transmission media includes, without limitation,coaxial cables, copper wire and fiber optics, including the wires thatcomprise the bus 124, as well as the various components of thecommunication subsystem 134 (and/or the media by which thecommunications subsystem 134 provides communication with other devices).Hence, transmission media can also take the form of waves (includingwithout limitation radio, acoustic and/or light waves, such as thosegenerated during radio-wave and infra-red data communications).

Common forms of physical and/or tangible computer readable mediainclude, for example, a floppy disk, a flexible disk, a hard disk,magnetic tape, or any other magnetic medium, a CD-ROM, any other opticalmedium, punch cards, paper tape, any other physical medium with patternsof holes, a RAM, a PROM, and EPROM, a FLASH-EPROM, any other memory chipor cartridge, a carrier wave as described hereinafter, or any othermedium from which a computer can read instructions and/or code.

Various embodiments of the disclosure could also include permutations ofthe various elements recited in the claims as if each dependent claimwas a multiple dependent claim incorporating the limitations of each ofthe preceding dependent claims as well as the independent claims. Suchpermutations are expressly within the scope of this disclosure.

While the disclosed embodiments have been particularly shown anddescribed with reference to a number of alternatives, it would beunderstood by those skilled in the art that changes in the form anddetails may be made to the various embodiments disclosed herein withoutdeparting from the spirit and scope of the disclosed embodiments andthat the various embodiments disclosed herein are not intended to act aslimitations on the scope of the claims. All references cited herein areincorporated in their entirety by reference.

The description of the present disclosed embodiments has been presentedfor purposes of illustration and description, but is not intended to beexhaustive or limiting of the disclosed embodiments to the formdisclosed. The scope of the present disclosed embodiments is limitedonly by the scope of the following claims. Many modifications andvariations will be apparent to those of ordinary skill in the art. Theembodiment described and shown in the figures was chosen and describedin order to best explain the principles of the disclosed embodiments,the practical application, and to enable others of ordinary skill in theart to understand the disclosed embodiments for various embodiments withvarious modifications as are suited to the particular use contemplated.

1. A method of imaging a breast comprising: providing an x-ray source;providing a full field digital x-ray detector; acquiring a sequence ofsub-images, having differing exposure parameters by projecting x-raysfrom the source to the detector at a selected view angle while varyingan exposure level between sub-images; and combining the sub-images intoa two-dimensional composite mammography image having greater dynamicrange than the dynamic range of any single sub-image.
 2. The method ofimaging a breast of claim 1 further comprising determining an exposureparameter of one or more sub-images prior to acquiring the sequence ofsub-images.
 3. The method of imaging a breast of claim 2 whereindetermining an exposure parameter of one or more sub-images comprisesdetermining a sub-exposure integration time or a sub-exposureirradiation level.
 4. The method of imaging a breast of claim 3 whereinthe determination of an exposure parameter is based upon one or more ofx-ray beam quality, x-ray beam intensity, information about the imagedobject, breast thickness, patient age and the response of the detector.5. (canceled)
 6. The method of imaging a breast of claim 1 where thedigital flat panel detector electron well density is below 500 electronsper square micron.
 7. An apparatus for imaging a breast comprising: anx-ray source; an x-ray detector; and image processing apparatusconfigured to: acquire a sequence of sub-images having differingexposure parameters by projecting x-rays from the x-ray source to thedetector at a selected view angle while varying an exposure levelbetween sub-images; and combine the sub-images into a two-dimensionalcomposite mammography image having greater dynamic range than thedynamic range of any single sub-image.
 8. (canceled)
 9. The apparatusfor imaging a breast of claim 7 wherein the x-ray detector comprises adigital flat panel detector having an electron well density below around500 electrons per square micron.
 10. (canceled)
 11. (canceled)
 12. Themethod of imaging a breast of claim 1 further comprising acquiring asequence of sub-images such that a frame integration time is variedbetween a first sub-image and a second sub-image and an x-ray beamenergy is held constant between the first sub-image and the secondsub-image.
 13. The method of imaging a breast of claim 12 furthercomprising limiting the frame integration time of the first sub-image toa frame integration time which is less than a frame integration timedetermined to cause sensor saturation when the sensor is unobstructed.14. The method of imaging a breast of claim 13 further comprisingcausing the frame integration time of the second sub-image to be:greater than the frame integration time of the first sub-image; andequal to or less than the frame integration time of the first sub-imagemultiplied by the projected signal level at a selected location for thecomposite mammography image showing a selected dense tissue divided bythe measured signal level at the selected location of the firstsub-image showing the selected dense tissue.
 15. The method of imaging abreast of claim 1 further comprising combining the sub-images into atwo-dimensional composite mammography image by adding the sub-images.16. The apparatus for imaging a breast of claim 7 wherein the imageprocessing apparatus is further configured to acquire a sequence ofsub-images such that a frame integration times is varied between a firstsub-image and a second sub-image and an x-ray beam energy is heldconstant between the first sub-image and the second sub-image.
 17. Theapparatus for imaging a breast of claim 16 wherein the image processingapparatus is further configured to limit the frame integration time ofthe first sub-image to a frame integration time which is less than aframe integration time determined to cause sensor saturation when thesensor is unobstructed.
 18. The apparatus for imaging a breast of claim16 wherein the image processing apparatus is further configured to causethe frame integration time of the second sub-image to be: greater thanthe frame integration time of the first sub-image; and equal to or lessthan the frame integration time of the first sub-image multiplied by theprojected signal level at a selected location for the compositemammography image showing a selected dense tissue divided by themeasured signal level at the selected location of the first sub-imageshowing the selected dense tissue.
 19. The apparatus for imaging abreast of claim 7 wherein the image processing apparatus is furtherconfigured to combining the sub-images into a two-dimensional compositemammography image by adding the sub-images.